|Publication number||US7556597 B2|
|Application number||US 10/982,639|
|Publication date||Jul 7, 2009|
|Filing date||Nov 5, 2004|
|Priority date||Nov 7, 2003|
|Also published as||US20050101831, WO2005048647A2, WO2005048647A3|
|Publication number||10982639, 982639, US 7556597 B2, US 7556597B2, US-B2-7556597, US7556597 B2, US7556597B2|
|Inventors||Scott Allan Miller, III, Bernd Waldmann, David L. Basinger|
|Original Assignee||Otologics, Llc|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (66), Referenced by (6), Classifications (7), Legal Events (13)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This application claims priority under 35 U.S.C. 119 to U.S. Provisional Application No. 60/518,537 entitled: “Active Vibration Attenuation for Implantable Microphone,” having a filing date of Nov. 7, 2003; the contents of which are incorporated herein as if set forth in full.
The present invention relates to implanted microphone assemblies, e.g., as employed in implantable hearing instruments, and more particularly, to implanted microphone assemblies having reduced sensitivity to vibration.
In the class of hearing aid systems generally referred to as implantable hearing instruments, some or all of various hearing augmentation componentry is positioned subcutaneously on, within, or proximate to a patient's skull, typically at locations proximate the mastoid process. In this regard, implantable hearing instruments may be generally divided into two sub-classes, namely semi-implantable and fully implantable. In a semi-implantable hearing instrument, one or more components such as a microphone, signal processor, and transmitter may be externally located to receive, process, and inductively transmit an audio signal to implanted components such as a transducer. In a fully implantable hearing instrument, typically all of the components, e.g., the microphone, signal processor, and transducer, are located subcutaneously. In either arrangement, an implantable transducer is utilized to stimulate a component of the patient's auditory system (e.g., ossicles and/or the cochlea).
By way of example, one type of implantable transducer includes an electromechanical transducer having a magnetic coil that drives a vibratory actuator. The actuator is positioned to interface with and stimulate the ossicular chain of the patient via physical engagement. (See e.g., U.S. Pat. No. 5,702,342). In this regard, one or more bones of the ossicular chain are made to mechanically vibrate, which causes the ossicular chain to stimulate the cochlea through its natural input, the so-called oval window.
As may be appreciated, hearing instruments that propose utilizing an implanted microphone will require that the microphone be positioned at a location that facilitates the receipt of acoustic signals. For such purposes, an implantable microphone may be positioned (e.g., in a surgical procedure) between a patient's skull and skin, for example, at a location rearward and upward of a patient's ear (e.g., in the mastoid region).
For a wearer a hearing instrument including an implanted microphone (e.g., middle ear transducer or cochlear implant stimulation systems), the skin and tissue covering the microphone diaphragm may increase the vibration sensitivity of the instrument to the point where body sounds and the wearer's own voice, conveyed via bone conduction, may saturate internal amplifier stages and thus lead to distortion. Also, in systems employing a middle ear stimulation transducer, the system may produce feedback by picking up and amplifying vibration caused by the stimulation transducer.
Certain proposed methods intended to mitigate vibration sensitivity may potentially also have an undesired effect on sensitivity to airborne sound as conducted through the skin. It is therefore desirable to have a means of reducing system response to vibration, without affecting sound sensitivity. This is the goal of the present invention.
In order to achieve this goal, it is necessary to differentiate between the desirable case, caused by outside sound, of the skin moving relative to an (stationary) implant housing, and the undesirable case, caused by bone vibration, of an implant housing moving relative to the (stationary) skin, which will result in the inertia of the skin exerting a force on the microphone diaphragm.
According to a primary aspect of the invention, differentiation between the desirable and undesirable cases is achieved by utilizing at least one motion sensor to produce a signal when an implanted microphone is in motion (e.g., relative to an intertial mass). Such a sensor may be, without limitation, an acceleration sensor and/or a velocity sensor. In any case, the signal is indicative movement of the implanted microphone diaphragm. In turn, this signal is used to yield a microphone output signal that is less vibration sensitive.
The motion sensor(s) may be interconnected to an implantable support member for co-movement therewith. For example, such support member may be a part of an implantable microphone or part of an implantable capsule to which the implantable microphone is mounted.
In the first arrangement, the implantable microphone may comprise a microphone housing, an external diaphragm disposed across an aperture of the housing, and a microphone transducer interconnected to the microphone housing and operable to provide an output signal responsive to movement of the diaphragm. Such output signal may be supplied to an implantable stimulation transducer for middle ear, inner ear and/or cochlear implant stimulation. In this arrangement, the motion sensor(s) may be interconnected to the microphone housing and/or the microphone transducer for co-movement therewith. An example of a middle ear stimulation transducer arrangement is described in U.S. Pat. No. 6,491,622, hereby incorporated by reference.
In the second arrangement, the implanted microphone may be supportably interconnected within an opening of an implant capsule, wherein the external diaphragm is located to receive incident acoustic waves and a microphone transducer is hermetically sealed within the implant capsule. In this arrangement, the motion sensor(s) may be interconnected to the implant capsule for co-movement therewith. Such implant capsule may also hermetically house other componentry (e.g., processor and/or circuit componentry, a rechargeable energy source and storage device, etc.) and may provide one or more signal terminal(s) for electrical interconnection (e.g., via one or more cables) with an implantable stimulation transducer for middle ear or cochlear implant stimulation.
In either arrangement, the motion sensor(s) may be positioned such that an axis of sensitivity of the sensor is aligned with a principal direction of movement of the microphone diaphragm. Such a principal direction of movement may be substantially normal to a surface (e.g., a planar surface) defined by the diaphragm. Such alignment of the motion sensor may allow for enhanced detection of undesired movement between the diaphragm and overlying tissue (e.g., skin). More preferably, such an axis of sensitivity may extend through the center of mass of the microphone. This may allow for more accurately identifying movement of the microphone as an assembly. Accordingly, the center of mass of the microphone assembly and motion sensor(s) may be located on a common axis that may also be directed normal to the principal direction of movement of the microphone diaphragm. In an arrangement where a plurality of motion sensor(s) are employed, the sensors may be positioned so that their centroid or combinative center of mass is located on such a common axis.
In another aspect utilizing a motion sensor to yield a microphone output signal that is less vibration sensitive, the output of the motion sensor may be processed with an output of the implantable microphone transducer to provide an audio signal that is less vibration-sensitive than the microphone output alone. For example, the motion sensor output may be appropriately scaled, phase shifted and/or frequency-shaped to match a difference in frequency response between the motion sensor output and the microphone transducer output, then subtracted from the microphone transducer output to yield a net, improved audio signal employable for driving a middle ear transducer, an inner ear transducer and/or a cochlear implant stimulation system.
In a yet further aspect of the invention, the motion sensor output may be utilized by a controller to provide a control output to at least one actuator. Such an actuator may be capable of moving an implantable microphone assembly housing or an implant capsule (e.g., relative to a vibrational source), so as to substantially reduce movement of the microphone diaphragm relative to the skin of a patient which covers the microphone diaphragm. By way of example only, a piezo-electric, electromagnetic, or acoustic actuator(s) may be employed.
As noted, in certain arrangements the motion sensor(s) may be interconnected to a part of an implantable microphone for co-movement therewith. In such arrangements, the actuator(s) may be interconnected to an implant capsule and actuatable to apply forces to the microphone (e.g., the microphone housing) so as to reduce undesired movement of the external diaphragm. In such arrangements, a compliant member may be interposed between the microphone assembly and that portion of the implant capsule to which the actuator(s) is interconnected. As further noted above, in certain arrangements the motion sensor(s) may be interconnected to an implant capsule. In turn the motion sensor(s) may be interconnected to a proof mass, i.e., a reference mass for the motion sensor(s). In such arrangements, the actuator(s) may be interconnected to the microphone (e.g., the microphone housing) and actuatable to apply forces against the implant capsule and/or the motion sensor (e.g., a proof mass of the sensor) to reduce undesired movement of the external diaphragm. Further, a compliant member may be interposed between the implant capsule and a patient's skull or other anatomical structure upon implantation, allowing forces of the actuator to move the implant capsule relative to the skull or other anatomical structure.
Preferably, in each of the noted arrangements utilizing an actuator(s), the actuator(s) may be desirably positioned to apply a force directed along an axis extending through the center of mass of the microphone. More preferably, this axis passing through the center of mass of the microphone may also be aligned with a principal direction of movement of the microphone diaphragm. Further, the motion sensor(s) and actuator(s) may be located on a common axis that may pass through the center of mass of the microphone and/or be aligned with the principal direction of movement of the diaphragm. Further, where a plurality of actuators are employed, the actuators may be desirably positioned so that the centroid or combinative center of mass of such actuators is located on such a common axis.
In a related aspect, a method for attenuating undesired movement of an implantable microphone is provided. The method includes generating a motion signal that is indicative of movement of an implantable support member associated with an implantable microphone diaphragm. Preferably, the implantable support member is substantially isolated from outside sound such that the motion of the member is primarily caused by undesirable sources of vibration. In response to the motion signal, a force is applied at least in part to the support member to reduce relative movement between the microphone diaphragm and tissue overlying the microphone diaphragm. In this regard, the microphone diaphragm may be moved in response to the undesired motion to reduce or attenuate relative movement between the microphone diaphragm and overlying tissue. As will be appreciated, such relative movement may result in the application of forces to the diaphragm, which may be represented as undesired sound (e.g., noise). By reducing this relative movement, the output of an implanted microphone may be enhanced for hearing purposes.
In order to reduce the relative movement between the microphone diaphragm and the overlying tissue, it may be desirable to monitor the motion of the support member in a direction most likely to result in undesired relative movement. For instance, a planar diaphragm may have a primary direction of movement in a direction that is substantially normal to its planar surface. Accordingly, undesired movement in this direction may be more likely to result in undesired forced being applied to the diaphragm that may in turn be represented as undesirable sound. In this regard, a sensor operative to generate a motion signal in this direction may be utilized.
Further, to reduce relative movement, it may be desirable to apply a force aligned with the primary direction of movement of the microphone diaphragm. That is, by moving the microphone diaphragm primarily in the direction that is most likely to result in undesirable sound, more relative movement may be attenuated. Accordingly, more undesirable sound may be removed from an output of the microphone.
Reference will now be made to the accompanying drawings, which at least assist in illustrating the various pertinent features of the present invention. In this regard, the following description of a hearing instrument is presented for purposes of illustration and description. Furthermore, the description is not intended to limit the invention to the form disclosed herein. Consequently, variations and modifications commensurate with the following teachings, and skill and knowledge of the relevant art, are within the scope of the present invention. The embodiments described herein are further intended to explain the best modes known of practicing the invention and to enable others skilled in the art to utilize the invention in such, or other embodiments and with various modifications required by the particular application(s) or use(s) of the present invention.
Hearing Instrument System:
In the illustrated system, a biocompatible implant capsule 100 is located subcutaneously on a patient's skull. The implant capsule 100 includes a signal receiver 118 (e.g., comprising a coil element) and a microphone diaphragm 12 that is positioned to receive acoustic signals through overlying tissue. The implant housing 100 may further be utilized to house a number of components of the fully implantable hearing instrument. For instance, the implant capsule 100 may house an energy storage device, a microphone transducer, and a signal processor. Various additional processing logic and/or circuitry components may also be included in the implant capsule 100 as a matter of design choice. Typically, a signal processor within the implant capsule 100 is electrically interconnected via wire 106 to a transducer 108.
The transducer 108 is supportably connected to a positioning system 110, which in turn, is connected to a bone anchor 116 mounted within the patient's mastoid process (e.g., via a hole drilled through the skull). The transducer 108 includes a connection apparatus 112 for connecting the transducer 108 to the ossicles 120 of the patient. In a connected state, the connection apparatus 112 provides a communication path for acoustic stimulation of the ossicles 120, e.g., through transmission of vibrations to the incus 122.
During normal operation, acoustic signals are received subcutaneously at the microphone diaphragm 12. Upon receipt of the acoustic signals, a signal processor within the implant capsule 100 processes the signals to provide a processed audio drive signal via wire 106 to the transducer 108. As will be appreciated, the signal processor may utilize digital processing techniques to provide frequency shaping, amplification, compression, and other signal conditioning, including conditioning based on patient-specific fitting parameters. The audio drive signal causes the transducer 108 to transmit vibrations at acoustic frequencies to the connection apparatus 112 to effect the desired sound sensation via mechanical stimulation of the incus 122 of the patient.
To power the fully implantable hearing instrument system of
One or more processor(s) and/or circuit component(s) 60 and an on-board energy storage device (not shown) may be supportably mounted to a circuit board 64 disposed within implant capsule 100. In the embodiment of
As may be appreciated, in the embodiments shown in
To actively address such transmitted vibration and, hence, undesired vibration of the diaphragm 12, each of the embodiments includes a motion sensor 70 that provides an output signal proportional to the vibrational movement of the support member to which it is attached. In the
In each of the arrangements, the motion sensor 70 may be located such that at least one axis of sensitivity of the motion sensor 70 is aligned with the principle direction of movement of the diaphragm 12. That is, at least one axis of sensitivity of the accelerometer 70 may be located such that it is sensitive to movement normal to the surface of the diaphragm 12. More preferably, this axis of sensitivity may also pass through a center of mass of the microphone assembly 10. In this regard, the movement of the microphone assembly 10 in the direction most likely to result in undesired vibration within the diaphragm 12 may be more accurately monitored. As may be appreciated, multiple motion sensor may be employed in the embodiments with corresponding analogous mounting arrangements to that shown for the motion sensor 70 in the given embodiment.
With particular respect to the embodiment of
Referring now to
Referring now to
In each of the
As shown in
Those skilled in the art will appreciate variations of the above-described embodiments that fall within the scope of the invention. As a result, the invention is not limited to the specific examples and illustrations discussed above, but only by the following claims and their equivalents.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US4442323 *||Jul 17, 1981||Apr 10, 1984||Pioneer Electronic Corporation||Microphone with vibration cancellation|
|US4443666||Nov 24, 1980||Apr 17, 1984||Gentex Corporation||Electret microphone assembly|
|US4450930||Sep 3, 1982||May 29, 1984||Industrial Research Products, Inc.||Microphone with stepped response|
|US4504703||Aug 16, 1984||Mar 12, 1985||Asulab S.A.||Electro-acoustic transducer|
|US4532930||Apr 11, 1983||Aug 6, 1985||Commonwealth Of Australia, Dept. Of Science & Technology||Cochlear implant system for an auditory prosthesis|
|US4606329||May 22, 1985||Aug 19, 1986||Xomed, Inc.||Implantable electromagnetic middle-ear bone-conduction hearing aid device|
|US4607383||Aug 18, 1983||Aug 19, 1986||Gentex Corporation||Throat microphone|
|US4621171||May 31, 1983||Nov 4, 1986||Tokoyo Shibaura Denki Kabushiki Kaisha||Electroacoustic transducer and a method for manufacturing thereof|
|US4774933||Nov 17, 1987||Oct 4, 1988||Xomed, Inc.||Method and apparatus for implanting hearing device|
|US4815560||Dec 4, 1987||Mar 28, 1989||Industrial Research Products, Inc.||Microphone with frequency pre-emphasis|
|US4837833||Jan 21, 1988||Jun 6, 1989||Industrial Research Products, Inc.||Microphone with frequency pre-emphasis channel plate|
|US4932405||Aug 7, 1987||Jun 12, 1990||Antwerp Bionic Systems N.V.||System of stimulating at least one nerve and/or muscle fibre|
|US4936305||Jul 20, 1988||Jun 26, 1990||Richards Medical Company||Shielded magnetic assembly for use with a hearing aid|
|US5015224||Aug 17, 1990||May 14, 1991||Maniglia Anthony J||Partially implantable hearing aid device|
|US5105811||May 16, 1991||Apr 21, 1992||Commonwealth Of Australia||Cochlear prosthetic package|
|US5163957||Sep 10, 1991||Nov 17, 1992||Smith & Nephew Richards, Inc.||Ossicular prosthesis for mounting magnet|
|US5176620||Oct 17, 1990||Jan 5, 1993||Samuel Gilman||Hearing aid having a liquid transmission means communicative with the cochlea and method of use thereof|
|US5219037 *||Jan 21, 1992||Jun 15, 1993||General Motors Corporation||Component mount assembly providing active control of vehicle vibration|
|US5277694||Feb 13, 1992||Jan 11, 1994||Implex Gmbh||Electromechanical transducer for implantable hearing aids|
|US5363452||May 19, 1992||Nov 8, 1994||Shure Brothers, Inc.||Microphone for use in a vibrating environment|
|US5402496||Jul 13, 1992||Mar 28, 1995||Minnesota Mining And Manufacturing Company||Auditory prosthesis, noise suppression apparatus and feedback suppression apparatus having focused adaptive filtering|
|US5411467||May 30, 1990||May 2, 1995||Implex Gmbh Spezialhorgerate||Implantable hearing aid|
|US5456654||Jul 1, 1993||Oct 10, 1995||Ball; Geoffrey R.||Implantable magnetic hearing aid transducer|
|US5475759||May 10, 1993||Dec 12, 1995||Central Institute For The Deaf||Electronic filters, hearing aids and methods|
|US5500902||Jul 8, 1994||Mar 19, 1996||Stockham, Jr.; Thomas G.||Hearing aid device incorporating signal processing techniques|
|US5554096||Apr 8, 1994||Sep 10, 1996||Symphonix||Implantable electromagnetic hearing transducer|
|US5558618||Jan 23, 1995||Sep 24, 1996||Maniglia; Anthony J.||Semi-implantable middle ear hearing device|
|US5624376||Jan 3, 1995||Apr 29, 1997||Symphonix Devices, Inc.||Implantable and external hearing systems having a floating mass transducer|
|US5647579 *||Mar 27, 1996||Jul 15, 1997||Nissan Motor Co., Ltd.||Control type vibro-isolating support|
|US5680467||Oct 17, 1996||Oct 21, 1997||Gn Danavox A/S||Hearing aid compensating for acoustic feedback|
|US5702431||Sep 17, 1996||Dec 30, 1997||Sulzer Intermedics Inc.||Enhanced transcutaneous recharging system for battery powered implantable medical device|
|US5749912||Aug 26, 1996||May 12, 1998||House Ear Institute||Low-cost, four-channel cochlear implant|
|US5762583||Aug 7, 1996||Jun 9, 1998||St. Croix Medical, Inc.||Piezoelectric film transducer|
|US5795287||Sep 30, 1996||Aug 18, 1998||Symphonix Devices, Inc.||Tinnitus masker for direct drive hearing devices|
|US5800336||Jan 3, 1996||Sep 1, 1998||Symphonix Devices, Inc.||Advanced designs of floating mass transducers|
|US5814095||Mar 13, 1997||Sep 29, 1998||Implex Gmbh Spezialhorgerate||Implantable microphone and implantable hearing aids utilizing same|
|US5842967||Aug 7, 1996||Dec 1, 1998||St. Croix Medical, Inc.||Contactless transducer stimulation and sensing of ossicular chain|
|US5848171||Jan 12, 1996||Dec 8, 1998||Sonix Technologies, Inc.||Hearing aid device incorporating signal processing techniques|
|US5857958||Dec 23, 1996||Jan 12, 1999||Symphonix Devices, Inc.||Implantable and external hearing systems having a floating mass transducer|
|US5859916||Jul 12, 1996||Jan 12, 1999||Symphonix Devices, Inc.||Two stage implantable microphone|
|US5881158||May 23, 1997||Mar 9, 1999||United States Surgical Corporation||Microphones for an implantable hearing aid|
|US5888187||Mar 27, 1997||Mar 30, 1999||Symphonix Devices, Inc.||Implantable microphone|
|US5897486||Mar 11, 1997||Apr 27, 1999||Symphonix Devices, Inc.||Dual coil floating mass transducers|
|US5906635||Aug 18, 1997||May 25, 1999||Maniglia; Anthony J.||Electromagnetic implantable hearing device for improvement of partial and total sensoryneural hearing loss|
|US5912977||Mar 11, 1997||Jun 15, 1999||Siemens Audiologische Technik Gmbh||Distortion suppression in hearing aids with AGC|
|US5913815||Dec 6, 1995||Jun 22, 1999||Symphonix Devices, Inc.||Bone conducting floating mass transducers|
|US5951601||Mar 24, 1997||Sep 14, 1999||Lesinski; S. George||Attaching an implantable hearing aid microactuator|
|US6044162||Dec 20, 1996||Mar 28, 2000||Sonic Innovations, Inc.||Digital hearing aid using differential signal representations|
|US6072884||Nov 18, 1997||Jun 6, 2000||Audiologic Hearing Systems Lp||Feedback cancellation apparatus and methods|
|US6072885||Aug 22, 1996||Jun 6, 2000||Sonic Innovations, Inc.||Hearing aid device incorporating signal processing techniques|
|US6093144 *||Dec 16, 1997||Jul 25, 2000||Symphonix Devices, Inc.||Implantable microphone having improved sensitivity and frequency response|
|US6097823||Dec 17, 1997||Aug 1, 2000||Texas Instruments Incorporated||Digital hearing aid and method for feedback path modeling|
|US6104822||Aug 6, 1997||Aug 15, 2000||Audiologic, Inc.||Digital signal processing hearing aid|
|US6108431||Oct 1, 1996||Aug 22, 2000||Phonak Ag||Loudness limiter|
|US6128392||Jun 4, 1998||Oct 3, 2000||Implex Aktiengesellschaft Hearing Technology||Hearing aid with compensation of acoustic and/or mechanical feedback|
|US6134329||Sep 5, 1997||Oct 17, 2000||House Ear Institute||Method of measuring and preventing unstable feedback in hearing aids|
|US6151400||Oct 24, 1995||Nov 21, 2000||Cochlear Limited||Automatic sensitivity control|
|US6163287||Apr 5, 1999||Dec 19, 2000||Sonic Innovations, Inc.||Hybrid low-pass sigma-delta modulator|
|US6173063||Oct 6, 1998||Jan 9, 2001||Gn Resound As||Output regulator for feedback reduction in hearing aids|
|US6198971||Aug 6, 1999||Mar 6, 2001||Implex Aktiengesellschaft Hearing Technology||Implantable system for rehabilitation of a hearing disorder|
|US6381336||Mar 2, 1999||Apr 30, 2002||S. George Lesinski||Microphones for an implatable hearing aid|
|US6422991||Jul 11, 2000||Jul 23, 2002||Symphonix Devices, Inc.||Implantable microphone having improved sensitivity and frequency response|
|US6626822||Jul 12, 2000||Sep 30, 2003||Symphonix Devices, Inc.||Implantable microphone having improved sensitivity and frequency response|
|US6707920||Dec 12, 2000||Mar 16, 2004||Otologics Llc||Implantable hearing aid microphone|
|US6807445||Mar 20, 2002||Oct 19, 2004||Cochlear Limited||Totally implantable hearing system|
|USRE33170||Dec 18, 1985||Feb 27, 1990||The Regents Of The University Of California||Surgically implantable disconnect device|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US7775964 *||Jan 11, 2006||Aug 17, 2010||Otologics Llc||Active vibration attenuation for implantable microphone|
|US7840020||Mar 28, 2006||Nov 23, 2010||Otologics, Llc||Low acceleration sensitivity microphone|
|US8641595||Jan 21, 2009||Feb 4, 2014||Cochlear Limited||Automatic gain control for implanted microphone|
|US8771166||May 28, 2010||Jul 8, 2014||Cochlear Limited||Implantable auditory stimulation system and method with offset implanted microphones|
|WO2011064409A2||Mar 17, 2011||Jun 3, 2011||Advanced Bionics Ag||Implantable microphone|
|WO2011064410A2||Mar 17, 2011||Jun 3, 2011||Advanced Bionics Ag||Implantable microphone|
|International Classification||H04R25/00, H04R|
|Cooperative Classification||H04R25/606, H04R19/016, H04R2225/67|
|Apr 29, 2005||AS||Assignment|
Owner name: OTOLOGICS, LLC, COLORADO
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:MILLER, SCOTT ALLAN III;WALDMANN, BERND;BASINGER, DAVID L.;REEL/FRAME:016502/0616
Effective date: 20050421
|Jul 8, 2005||AS||Assignment|
|Jan 25, 2006||AS||Assignment|
|Mar 10, 2006||AS||Assignment|
|Jun 9, 2006||AS||Assignment|
|Jun 15, 2006||AS||Assignment|
|Jul 13, 2006||AS||Assignment|
|Aug 30, 2006||AS||Assignment|
|Mar 16, 2007||AS||Assignment|
|Jan 22, 2010||AS||Assignment|
Owner name: COCHLEAR LIMITED,AUSTRALIA
Free format text: SECURITY AGREEMENT;ASSIGNOR:OTOLOGICS, L.L.C.;REEL/FRAME:023832/0387
Effective date: 20100119
|Mar 11, 2010||AS||Assignment|
Owner name: OTOLOGICS, LLC,COLORADO
Free format text: ACKGT. OF INEFFECTIVE PAT. ASSMT. AGMT;ASSIGNOR:MEDTRONIC, INC.;REEL/FRAME:024066/0349
Effective date: 20100302
Owner name: OTOLOGICS, LLC, COLORADO
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Effective date: 20100302
|Oct 3, 2012||AS||Assignment|
Owner name: OTOLOGICS, L.L.C., COLORADO
Free format text: RELEASE BY SECURED PARTY;ASSIGNOR:COCHLEAR LIMITED;REEL/FRAME:029072/0633
Effective date: 20120928
Owner name: COCHLEAR LIMITED, AUSTRALIA
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|Dec 27, 2012||FPAY||Fee payment|
Year of fee payment: 4